Normalization fitting method

ABSTRACT

A method, including obtaining data indicative of respective perceived loudness levels for a plurality of hearing percepts respectively evoked at different current levels, and creating a map for the hearing prosthesis based on the obtained data by adjusting at least one of the respective current levels based on data of a respective perceived loudness for another current level.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority to Provisional U.S. patent applicationSer. No. 62/160,758, entitled NORMALIZATION FITTING METHOD, filed on May13, 2015, naming Filiep J. VANPOUCKE of Belgium as an inventor, theentire contents of that application being incorporated herein byreference in its entirety.

BACKGROUND

Hearing loss, which may be due to many different causes, is generally oftwo types: conductive and sensorineural. Sensorineural hearing loss isdue to the absence or destruction of the hair cells in the cochlea thattransduce sound signals into nerve impulses. Various hearing prosthesesare commercially available to provide individuals suffering fromsensorineural hearing loss with the ability to perceive sound. Oneexample of a hearing prosthesis is a cochlear implant.

Conductive hearing loss occurs when the normal mechanical pathways thatprovide sound to hair cells in the cochlea are impeded, for example, bydamage to the ossicular chain or the ear canal. Individuals sufferingfrom conductive hearing loss may retain some form of residual hearingbecause the hair cells in the cochlea may remain undamaged.

Individuals suffering from hearing loss typically receive an acoustichearing aid. Conventional hearing aids rely on principles of airconduction to transmit acoustic signals to the cochlea. In particular, ahearing aid typically uses an arrangement positioned in the recipient'sear canal or on the outer ear to amplify a sound received by the outerear of the recipient. This amplified sound reaches the cochlea causingmotion of the perilymph and stimulation of the auditory nerve. Cases ofconductive hearing loss typically are treated by means of boneconduction hearing aids. In contrast to conventional hearing aids, thesedevices use a mechanical actuator that is coupled to the skull bone toapply the amplified sound.

In contrast to hearing aids, which rely primarily on the principles ofair conduction, certain types of hearing prostheses commonly referred toas cochlear implants convert a received sound into electricalstimulation. The electrical stimulation is applied to the cochlea, whichresults in the perception of the received sound.

It is noted that in at least some instances, there is utilitarian valueto fitting a hearing prosthesis to a particular recipient. In someexamples of some fitting regimes, there are methods which entail aclinician or some other professional presenting sounds to a recipient ofthe hearing prosthesis such that the hearing prosthesis evokes a hearingpercept. Information can be obtained from the recipient regarding thecharacter of the resulting hearing percept. Based on this information,the clinician can adjust or otherwise establish settings of the hearingprosthesis such that the hearing prosthesis operates according to thesesettings during normal use.

SUMMARY

In accordance with an exemplary embodiment, there is a method,comprising obtaining data indicative of respective perceived loudnesslevels for a plurality of hearing percepts respectively evoked atdifferent current levels, and creating a map for the hearing prosthesisbased on the obtained data by adjusting at least one of the respectivecurrent levels based on data of a respective perceived loudness foranother current level.

In accordance with another exemplary embodiment, there is a methodcomprising, obtaining data indicative of respective perceived loudnesslevels for a plurality of hearing percepts respectively evoked based onrespective different stimulus having respective first different loudnesslevels, wherein the respective evoked hearing percepts are evoked withrespective different energy outputs of a hearing prosthesis, obtainingdata indicative of normalized loudness levels for normal hearers for therespective different stimulus having respective different first loudnesslevels, and configuring the hearing prosthesis to automatically evokehearing percepts, in response to sound captured by the hearingprosthesis having respective second different loudness levelscorresponding to the respective first different loudness levels, atrespective new different energy levels different from those used toevoke the respective hearing percepts, for respective new respectivestimulus having the respective first different loudness levels, based onthe obtained data indicative of normalized loudness levels.

In accordance with another exemplary embodiment, there is a fittingsystem, comprising a sub-system configured to obtain statisticalperceived loudness data, a sub-system configured to obtain hearingprosthesis recipient-specific loudness data for a plurality of differentstimulus having at least some loudness levels corresponding to those ofthe statistical perceived loudness data, and a sub-system configured toautomatically configure a hearing prosthesis based on the obtainedstatistical data and the obtained recipient-specific loudness data.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments are described below with reference to the attached drawings,in which:

FIG. 1 is a perspective view of an exemplary hearing prosthesis in whichat least some of the teachings detailed herein are applicable;

FIG. 2 presents an exemplary electrode array according to an exemplaryembodiment;

FIG. 3 presents an exemplary device in use according to an exemplaryembodiment;

FIG. 4 presents exemplary loudness scaling tests results along withstatistical loudness data;

FIG. 5 presents, by way of a functional schematic, an exemplary systemaccording to an exemplary embodiment;

FIG. 6 presents a flowchart according to an exemplary embodiment;

FIG. 7 presents another flowchart according to another exemplaryembodiment;

FIG. 8A presents exemplary loudness scaling tests results along withstatistical loudness data along with graphical symbols conveying ahigh-level concept of an exemplary method of normalizing loudness with ahearing prosthesis;

FIG. 8B presents an exemplary gain change chart for a range of loudnesslevels in an exemplary scenario in which the teachings detailed hereinare utilized;

FIGS. 9A, 10A and 11A present composite data pertaining to perceivedloudness levels for different presentation levels;

FIGS. 9B, 10B and 11B present exemplary gain change charts for a rangeof loudness levels in various exemplary scenarios in which the teachingsdetailed herein are utilized;

FIGS. 9C, 10C and 11C present exemplary current levels according toexemplary scenarios in which the teachings detailed herein are utilized;

FIGS. 9D, 10D and 11D present exemplary current level functionsaccording to exemplary scenarios in which the teachings detailed hereinare utilized;

FIG. 12 presents exemplary threshold level and comfort level curves forexemplary scenarios in which the teachings detailed herein are utilized;

FIG. 13 presents an exemplary function having utilitarian value in someexemplary embodiments of the teachings detailed herein; and

FIG. 14 presents a flowchart for another exemplary method according toanother exemplary embodiment.

DETAILED DESCRIPTION

FIG. 1 is a perspective view of a cochlear implant, referred to ascochlear implant 100, implanted in a recipient, to which someembodiments detailed herein and/or variations thereof are applicable.The cochlear implant 100 is part of a system 10 that can includeexternal components, in some embodiments, as will be detailed below. Itis noted that the teachings detailed herein are applicable, in at leastsome embodiments, to partially implantable and/or totally implantablecochlear implants (i.e., with regard to the latter, such as those havingan implanted microphone). It is further noted that the teachingsdetailed herein are also applicable to other stimulating devices thatutilize an electrical current beyond cochlear implants (e.g., auditorybrain stimulators, pacemakers, etc.).

The recipient has an outer ear 101, a middle ear 105 and an inner ear107. Components of outer ear 101, middle ear 105 and inner ear 107 aredescribed below, followed by a description of cochlear implant 100.

In a fully functional ear, outer ear 101 comprises an auricle 110 and anear canal 102. An acoustic pressure or sound wave 103 is collected byauricle 110 and channeled into and through ear canal 102. Disposedacross the distal end of ear channel 102 is a tympanic membrane 104which vibrates in response to sound wave 103. This vibration is coupledto oval window or fenestra ovalis 112 through three bones of middle ear105, collectively referred to as the ossicles 106 and comprising themalleus 108, the incus 109 and the stapes 111. Bones 108, 109 and 111 ofmiddle ear 105 serve to filter and amplify sound wave 103, causing ovalwindow 112 to articulate, or vibrate in response to vibration oftympanic membrane 104. This vibration sets up waves of fluid motion ofthe perilymph within cochlea 140. Such fluid motion, in turn, activatestiny hair cells (not shown) inside of cochlea 140. Activation of thehair cells causes appropriate nerve impulses to be generated andtransferred through the spiral ganglion cells (not shown) and auditorynerve 114 to the brain (also not shown) where they are perceived assound.

As shown, cochlear implant 100 comprises one or more components whichare temporarily or permanently implanted in the recipient. Cochlearimplant 100 is shown in FIG. 1 with an external device 142, that is partof system 10 (along with cochlear implant 100), which, as describedbelow, is configured to provide power to the cochlear implant, where theimplanted cochlear implant includes a battery or other energy storagedevice (e.g., capacitor) that is charged (e.g., recharged) by the powerprovided from the external device 142.

In the illustrative arrangement of FIG. 1, external device 142 cancomprise a power source (not shown) disposed in a Behind-The-Ear (BTE)unit 126. External device 142 also includes components of atranscutaneous energy transfer link, referred to as an external energytransfer assembly. The transcutaneous energy transfer link is used totransfer power and/or data to cochlear implant 100. Various types ofenergy transfer, such as infrared (IR), electromagnetic, capacitive andinductive transfer, may be used to transfer the power and/or data fromexternal device 142 to cochlear implant 100. In the illustrativeembodiments of FIG. 1, the external energy transfer assembly comprisesan external coil 130 that forms part of an inductive radio frequency(RF) communication link. External coil 130 is typically a wire antennacoil comprised of multiple turns of electrically insulatedsingle-strand/or multi-strand platinum or gold wire. External device 142also includes a magnet (not shown) positioned within the turns of wireof external coil 130. It should be appreciated that the external deviceshown in FIG. 1 is merely illustrative, and other external devices maybe used with embodiments of the present invention.

Cochlear implant 100 comprises an internal energy transfer assembly 132which can be positioned in a recess of the temporal bone adjacentauricle 110 of the recipient. As detailed below, internal energytransfer assembly 132 is a component of the transcutaneous energytransfer link and receives power and/or data from external device 142.In the illustrative embodiment, the energy transfer link comprises aninductive RF link, and internal energy transfer assembly 132 comprises aprimary internal coil 136. Internal coil 136 is typically a wire antennacoil comprised of multiple turns of electrically insulatedsingle-strand/or multi-strand platinum or gold wire.

Cochlear implant 100 further comprises a main implantable component 120and an elongate electrode assembly 118. In some embodiments, internalenergy transfer assembly 132 and main implantable component 120 arehermetically sealed within a biocompatible housing. In some embodiments,main implantable component 120 includes an implantable microphoneassembly (not shown) and a sound processing unit (not shown) to convertthe sound signals received by the implantable microphone in internalenergy transfer assembly 132 to data signals. That said, in somealternative embodiments, the implantable microphone assembly can belocated in a separate implantable component (e.g., that has its ownhousing assembly, etc.) that is in signal communication with the mainimplantable component 120 (e.g., via leads or the like between theseparate implantable component and the main implantable component 120).In at least some embodiments, the teachings detailed herein and/orvariations thereof can be utilized with any type of implantablemicrophone arrangement.

Main implantable component 120 further includes a stimulator unit (alsonot shown) which generates electrical stimulation signals based on thedata signals. The electrical stimulation signals are delivered to therecipient via elongate electrode assembly 118.

Elongate electrode assembly 118 has a proximal end connected to mainimplantable component 120, and a distal end implanted in cochlea 140.Electrode assembly 118 extends from main implantable component 120 tocochlea 140 through mastoid bone 119. In some embodiments, electrodeassembly 118 may be implanted at least in basal region 116, andsometimes further. For example, electrode assembly 118 may extendtowards apical end of cochlea 140, referred to as cochlea apex 134. Incertain circumstances, electrode assembly 118 may be inserted intocochlea 140 via a cochleostomy 122. In other circumstances, acochleostomy may be formed through round window 121, oval window 112,the promontory 123 or through an apical turn 147 of cochlea 140.

Electrode assembly 118 comprises a longitudinally aligned and distallyextending array 146 of electrodes 148, disposed along a length thereof.As noted, a stimulator unit generates stimulation signals which areapplied by electrodes 148 to cochlea 140, thereby stimulating auditorynerve 114.

Because the cochlea is tonotopically mapped (i.e., spatial locationsthat are responsive to stimulus signals in a particular frequency rangeare identified), frequencies may be allocated to one or more electrodesof the electrode assembly to generate an electric field in positions inthe cochlea that are close to the region that would naturally bestimulated in normal hearing. This enables the prosthetic hearingimplant to bypass the hair cells in the cochlea to directly deliverelectrical stimulation to auditory nerve fibers, thereby allowing thebrain to perceive hearing sensations resembling natural hearingsensations. In achieving this, processing channels of the soundprocessing unit of the BTE 126 (i.e., specific frequency bands withtheir associated signal processing paths), are mapped to a set of one ormore electrodes to stimulate a desired nerve fiber or nerve region ofthe cochlea. Such sets of one or more electrodes for use in stimulationare referred to herein as “electrode channels” or “stimulationchannels.” In at least some exemplary embodiments, each channel has a“base” electrode corresponding to the electrode of the electrode arraythat is proximate the tonotopically mapped cochlea for a given frequencyor frequency range.

FIG. 2 illustrates a more detailed view, albeit functionally, of anexemplary electrode array 146 comprising a plurality of electrodes 148labeled 1-22, in accordance with an embodiment. In an exemplaryembodiment, each electrode 148 is an electrode that corresponds to aspecific frequency band channel of the cochlear implant 100, whereelectrode 22 corresponds to the lowest frequency band (channel), andelectrode 1 corresponds to the highest frequency band (channel), as willbe discussed in greater detail below. Briefly, it is noted that duringstimulation by the electrodes to evoke a hearing percept, one or moreelectrodes 148 is activated at a given electrode stimulation level(e.g., current level). This electrode stimulation level is pre-setduring a fitting process. For example, in at least some instances, anaudiologist adjusts stimulation channel electrode current levels of thecochlear implant 100 based on empirical data. More specifically, in atleast some embodiments, stimulation channel electrode current levels areadjusted by an audiologist based on threshold and comfort levels. Then,in at least some embodiments, the cochlear implant 100 is configuredsuch that respective stimulation channels of the cochlear implant 100have those respective current levels. This can be done, for example, byprogramming the cochlear implant 100 or by any other process that setsthe channels of the cochlear implant 100 to have the pertinentelectrical stimulation levels. Any arrangement of the cochlear implant100 and/or other equipment/devices that will enable the teachingsdetailed herein and/or variations thereof to be practiced can be used inat least some embodiments.

In view of this, an exemplary embodiment entails a fitting method thatentails setting or otherwise adjusting the parameters of the cochlearimplant 100 determining the electrical mapping from sound levels in oneor more or all of the frequency bands to electrical stimulation levels.This exemplary fitting method can include an audiologist or otherclinical professional tuning the electrical map parameters of thecochlear implant 100 to the particular auditory physiology of therecipient. More specifically, in at least some exemplary embodiments, aswill be detailed below, the fitting methods detailed herein are directedtowards obtaining a convergence between a perceived loudness, and aloudness corresponding to that of normal hearing people for a givenstimulus and/or for a range of stimuli.

FIG. 3 is a schematic diagram illustrating one exemplary arrangement 300in which a hearing implant fitting system 306 may be used to fit acochlear implant, in accordance with an embodiment. As shown in FIG. 3,an audiologist or clinician 304 may use a hearing implant fitting system306 (“fitting system” herein) comprising interactive software andcomputer hardware to create individualized recipient map data 322 thatare digitally stored on system 306, and ultimately downloaded to thememory of the sound processing unit 126 for recipient 302. System 306may be programmed and/or implement software programmed to carry out oneor more of the functions of mapping, neural response measuring, acousticstimulating, and recording of neural response measurements and otherstimuli.

In the embodiment illustrated in FIG. 3, sound processing unit 126 ofcochlear implant 100 may be connected directly to fitting system 306 toestablish a data communication link 308 between the sound processingunit 126 and fitting system 306. System 306 is thereafterbi-directionally coupled by a data communication link 308 with soundprocessing unit 126. It should be appreciated that although soundprocessing unit 126 and fitting system 306 are connected via a cable inFIG. 3, any communications link now or later developed may be utilizedto communicably couple the implant and fitting system.

Some exemplary embodiments will now be described in terms of utilizingthe aforementioned fitting system 306 to fit the aforementioned cochlearimplant 100 to achieve the aforementioned normalization convergence. Itis noted that the following is but exemplary, and that alternativemethods can be practiced utilizing other devices other than the fittingsystem 306 and/or alternative methods can be practiced to fit aprosthesis that is different than cochlear implant 100.

Briefly, at least some teachings detailed herein and/or variationsthereof are applicable to the development of a map for a unilateralcochlear implant user that restores the loudness percept or otherwiseadjust the loudness percept of a hearing percept evoked by the cochlearimplant towards a value that is closer to that of a normal hearingperson. As will be detailed herein, the teachings detailed herein and/orvariations thereof can be applicable to other types of hearingprostheses other than a cochlear implant. Still further, the teachingsdetailed herein and/or variations thereof can be applicable in at leastsome embodiments to hybrid devices and bimodal devices that utilize thecochlear implant along with another type of hearing device (e.g., atraditional hearing aid).

More specifically, in at least some exemplary embodiments, there is analgorithm that enables the development, including the automaticdevelopment, of a new electrical output map such that the loudnessratings of the cochlear implant recipient are normalized (when the newmap is utilized to evoke new hearing percepts). In at least someexemplary embodiments, the aforementioned loudness is normalized tovalues within the 95% confidence interval in a single step. By way ofexample only and not by way of limitation, a loudness scaling test (moreon this below) need only be administered one time to develop a newelectrical output regime that will result in the hearing percept thatwill more closely resemble that of the normal hearing person, and notmultiple times (although the single test may include repeated providingof tones at a specific loudness for a specific frequency, as detailedbelow).

In an exemplary embodiment, a diagnostic loudness scaling test isperformed on a recipient of the cochlear implant 100, which diagnosticloudness scaling test can be executed utilizing the fitting system 306and/or another system. An exemplary embodiment utilizes the AdaptiveCategorical Loudness Scaling test (ACALOS). Any loudness test that willenable the teachings detailed herein and/or variations thereof to bepracticed can be utilized in at least some embodiments.

More specifically, in an exemplary embodiment, a recipient of thecochlear implant 100 having an initial electrode current levelregime/embryonic map is subjected to multiple sound presentationscorresponding to a plurality of different sound stimuli, typicallydiscrete and temporally segregated from one another, respectively havingdifferent respective loudness levels (and thus the recipient is exposedto multiple sound presentation levels). The cochlear implant 100 evokesrespective hearing percepts (or attempts to evoke such—sometimes ahearing percept cannot be evoked because the given sound stimuli isbelow a threshold level) utilizing the initial electrode charge levelregime/embryonic map thereof. The recipient indicates his or herperception of loudness of each resulting hearing percept. By way ofexample only and not by way of limitation, in an exemplary embodiment, aplurality of noise bands are presented to the recipient of the hearingprosthesis at multiple presentation levels, ranging from 30 to 80 dBSPL,in steps of 5 dB, although the range can be different than this (e.g.,20 to 100 dBSPL, 25 to 75 dBSPL, any value or range of values that canenable the teachings detailed herein and/or variations therof) and/orthe increments can be different than this (e.g., increments of 2.5 dB,7.5 dB, 10 dB, etc.). Any value or range of values in any increment thatcan enable the teachings detailed herein and/or variations thereof canbe utilized in at least some embodiments.

In an exemplary embodiment, the various presentation levels are randomlyselected and randomly presented to the recipient. In alternativeembodiments, the various presentation levels are presented in anascending and/or a descending order. As will be detailed herein, in anexemplary embodiment includes a device and/or a system thatautomatically provides the various presentation levels to the recipient.

In an exemplary embodiment, each stimuli is presented twice or three orfour or five or more times (i.e., each presentation level is presentedtwice), and the results (i.e., the perceived respective loudness levels)are averaged. That said, in an alternative embodiment, each stimulus isonly presented once. The results of the various presentations arecompiled into a loudness growth function, in at least some exemplaryembodiments, the scaling test is repeated for 2 or more frequencyregions (e.g., for every octave, for 250 Hz, 1000 Hz and 4000 Hz, etc.).

FIG. 4 presents an exemplary chart presenting results of an exemplaryscaling test for tones presented at 1000 Hz (the tones were presentedtwice, and the averaged loudness score was averaged). In this regard,curve 410 constitutes empirical results from the scaling test, wherestimuli level (dBHL) is correlated to indicated loudness score on ascale of 0-6, with 0 being non-audible, 1 being very soft, 2 being soft,3 being normal sounding, 4 being loud, 5 being very loud and 6 being tooloud. Each circle represents an empirical data point, and the solidlines connecting each circle represent linear interpolation curvefitting. It is noted that in an alternative embodiment, other curvefitting techniques can be utilized, including those that do notnecessarily result in curves that pass through each specific empiricaldata point. Any curve fitting technique that can enable the teachingsdetailed herein and/or variations thereof can be utilized in at leastsome embodiments. Further, consistent with the description above, while5 dB increments have been utilized over a range of 20 dBHL to 80 dBHL,other increments and/or other ranges could have been utilized togenerate the curve 410.

The solid the black vertical lines at 20 dBHL and 75 dBHL in FIG. 4represents sound levels beyond which distinguishing loudness/softness isnot deemed utilitarian in this exemplary embodiment.

FIG. 4 contains three additional curves beyond 410: curve 412, curve 414and curve 416. Curve 412 entails statistical data corresponding to thefiftieth percentile normal hearing person. That is, in an exemplaryembodiment, based on a statistically significant group of representativenormal hearers (e.g., those that do not utilize a hearing prosthesis tohear), a mean, median and/or modal average of normal hearers would ratea given loudness level according to that presented along the curve 412.Curve 414 corresponds to a curve that relates to a statisticallysignificant group of representative normal hearers, where 97.5 percentof such people rate the given loudness level as a value at or above thatcurve. Conversely, curve 416 corresponds to a curve that relates to astatistically significant group of representative normal hearers, where97.5 percent of such people rate the given loudness level as a value ator below that curve, the difference between curve 414 and curve 416being that the people represented by curve 414 perceived the givenloudness levels as softer than the average normal hearer, and the peoplerepresented by curve 416 perceived the given loudness levels as louderthan the average normal hearer. Put another way, according to theexemplary embodiment, 95% of normal hearing people will rate a givenloudness level as having a value between and on curves 414 and 416.Other statistical populations can be utilized (e.g., the curves 414 and416 can correspond to curves that relate to a statistically significantgroup of representative normal hearers, where 90% of such people ratethe given loudness level as a value above the curve/below the curve, 99%of such people rate the given loudness level as a value above thecurve/below the curve etc.). In this regard, the curves 414 and 416represent statistical confidence intervals associated with thestatistical average data. Tighter or looser confidence margins can beutilized depending on a particular embodiment. In this regard, curves414 and 416 represent a 95% confidence interval.

An exemplary embodiment entails utilizing the empirical curve 410 (or,more generally, the empirical data associated with the empirical curve410) in combination with one or more of the statistical curves 412, 414or 416 (or, more generally, the statistical data associated with thestatistical curves) to adjust or otherwise change the initial electrodecharge level regime/embryonic map of the cochlear implant 100 utilizedto develop the empirical curve 410 (the empirical data associatedtherewith) such that the resulting hearing percepts will have loudnessvalues more in line with those statistical curves (statistical data).

Thus, briefly, with reference to FIG. 5, in an exemplary embodiment,fitting system 306 can be functionally characterized as a system 500,comprising a subsystem 510 configured to obtain recipient-specificloudness data (as represented by the arrow pointing towards black box510) for a plurality of different stimuli having at least some loudnesslevels corresponding to those of the statistical perceived loudnessdata, a subsystem 520 configured to obtain statistical perceivedloudness data (as represented by the arrow pointing towards black box520, and a subsystem 530 configured to automatically configure a hearingprosthesis (as represented by the arrow pointing away from black box530) based on the obtained statistical data and the obtainedrecipient-specific loudness data (as represented by the arrowsrespectively pointing from black boxes 510 and 520 to black box 530).

In an exemplary embodiment, system 500 can be a personal computer, alaptop computer, a mainframe computer, a network and/or units connectedby a network (as represented by the dashed lines—each component of thesystem 500 can be located at separate remote facilities), or a portablecomputing device (e.g., a smartphone having sufficient computationalpower), in which case, in some embodiments, system 500 can correspond toboth fitting system 306 and user interface 312 with respect to FIG. 3.System 500 can alternatively be a portion of one or more of theaforementioned devices. In an exemplary embodiment, subsystem 510 canobtain the recipient specific loudness data as a result of the system500 having the functionality to administer the aforementioned scalingtest. In an exemplary embodiment, this can be done autonomously in aninteractive manner with the recipient without a clinician operating themachine. Alternatively and/or in addition to this, the system 500 can beoperated by a clinician. Alternatively and/or in addition to this,subsystem 510 can obtain the recipient specific loudness data as aresult of data being uploaded to the system 500 (e.g., the subsystem 510can obtain the loudness data via a USB communication or the like and/orvia an ethernet connection or the like and/or via an optical media datastorage device etc.). In this regard, unless otherwise specified, asutilized herein, the phrase “obtaining data” encompasses both the actionof performing an empirical test to develop the data as well as theaction of obtaining data indicative of a prior test without actuallyexecuting the empirical test.

In an exemplary embodiment, subsystem 520 can obtain the statisticalperceived loudness data as a result of data being uploaded (e.g., thesubsystem 520 can obtain the statistical data via a USB communication orthe like, and/or via an ethernet connection or the like, and/or via anoptical media data storage device, etc.).

Any device, system, and/or method that will enable the statistical dataand/or the recipient specific loudness data to be obtained by thesystem, can be utilized in at least some embodiments, providing that theteachings detailed herein and/or variations thereof can be practicedutilizing such.

Subsystem 530 is configured to receive data from subsystem 510 and 520and to automatically configure the cochlear implant 100 based on theobtained statistical data and the obtained recipient-specific loudnessdata via the use of an exemplary algorithm as detailed below and/or viaother types of algorithms. In an exemplary embodiment, subsystem 530 isa CPU of a personal computer, or a processor of a portable computingdevice, or a processor linked to the subsystems 510 and 520 via anetwork (e.g., internet, etc.). In an exemplary embodiment, subsystem530 utilizes an algorithm to develop a map based on the data fromsubsystem 510 and 520 that will enable the recipient to perceive hearingpercepts at a loudness closer to that of the normal hearing recipientrelative to that which was the case utilizing the embryonic map/initialelectrode current regime used to develop the data obtained by the firstsubsystem 510.

Some exemplary methods and algorithms usable with the system 500 and/orusable aside from the system 500 will now be described.

FIG. 6 presents a flowchart 600 containing an exemplary algorithm for anexemplary method. Flowchart 600 includes action 610, which entailsobtaining data indicative of respective perceived loudness levels for aplurality of hearing percepts respectively evoked at different currentlevels. In an exemplary embodiment, this entails subjecting therecipient of a cochlear implant 100 to the scaling test detailed above,where the different current levels correspond to a phenomenon associatedwith the cochlear implant 100 where increased current level iscorrelated to increased perceived loudness of the different stimuli uponwhich the hearing percepts are based. With respect to FIG. 4, increasedloudness levels correspond to the utilization of increased currentlevels to evoke the respective hearing percepts, at least according tothe exemplary embryonic map utilized to evoke those hearing percepts forthe scaling test. It is also noted that while in at least someembodiments, method action 610 is accomplished by subjecting therecipient to the scaling test noted above, in an alternate embodiment,method action 610 is accomplished by obtaining the data compiled as aresult of the scaling test. That is, the actual scaling test need not beexecuted as part of method action 610 (e.g., the scaling test can beexecuted prior to the execution of method action 610). Accordingly, itis not necessary to directly conduct the scaling test to execute methodaction 610. Simply obtaining the data from the source that obtain thedata (either directly or indirectly (e.g., from another source)) viascaling test is sufficient to execute method action 610 in at least someembodiments.

After method action 610 is executed, flow chart 600 proceeds to methodaction 620, which entails creating a map (e.g., a new map) for thehearing prosthesis based on the obtained data obtained in method action610 by adjusting at least one of the respective current levels based ondata of a respective perceived loudness correlated to another currentlevel different from the respective current level. More specifically, inan exemplary embodiment, method action 620 can be executed via thealgorithm represented by flowchart 700 of FIG. 7. Flowchart 700 includesmethod action 710, which entails obtaining offset data from one or morepresentation levels relative to the statistical data (i.e., the normalhearing data, such as curve 410 of FIG. 4). FIG. 8A schematicallyillustrates method action 710 with respect to the presentation levelassociated with 40 dBHL and the presentation level associated with 65dBHL. More specifically, with respect to the loudness reading at thepresentation level of 40 dB, the recipient indicated that the perceivedloudness of the hearing percept evoked by that stimulus was below very,very soft (0.5 on the chart, between 0 and 1). Conversely, the averagenormal hearing person would have perceived the loudness level of thestimuli (the sound at 40 dBHL) as being about soft (almost level 2 onthe chart). The difference between these two data points is representedby the vertical arrow 810 extending from the empirical data point at 40dBHL. In an exemplary algorithm, the empirical curve 410 is utilized inmethod action 710 to obtain a loudness level corresponding to that whichthe recipient would rate the same as, or at least approximately the sameas, that of the normal hearing person. With regard to the exemplaryempirical curve 410 of FIG. 8, this corresponds to a loudness level of52 dBHL, as is represented by the horizontal arrow 812 extending fromthe aforementioned vertical arrow 810, and the downwardly pointingvertical arrow 814 extending from the horizontal arrow.

FIG. 8A also schematically illustrates method action 710 with respect tothe presentation level associated with 65 dBHL, where the recipientindicated that the perceived loudness of the hearing percept evoked bythat stimulus was loud (4 on the chart). Conversely, the average normalhearing person would have perceived the loudness level of the stimuli(the sound at 65 dBHL) as being of normal loudness. The differencebetween these two data points is represented by the vertical arrow 820extending from the empirical data point at 65 dBHL. In an exemplaryalgorithm, the empirical curve 410 is utilized in method action 710 toobtain a loudness level corresponding to that which the recipient wouldrate the same as, or at least approximately the same as, that of thenormal hearing person. With regard to the exemplary empirical curve 410of FIG. 8, this corresponds to a loudness level of 62 dBHL, as isrepresented by the horizontal arrow 822 extending from theaforementioned vertical arrow 820, and the downwardly pointing verticalarrow 824 extending from the horizontal arrow.

Accordingly, in an exemplary embodiment, method action 710 is executedto develop proxy loudness levels based on the statistical data and theempirical data, where the proxy loudness levels correspond to increasedlevels where the cochlear implant recipient has rated the perceivedloudness of a given loudness level as having a rating below that whichthe normal hearing person would have rated that level, and decreasedlevels where the cochlear implant recipient has rated the perceivedloudness of a given loudness level as having a rating above that whichthe normal hearing person would have rated that level.

In an exemplary embodiment, the steps of method action 710 can berepeated for each presentation level/loudness level associated with theempirical curve 410. That said, in an alternative embodiment, not allpresentation levels/loudness levels are subjected to the steps of methodaction 710.

Still with reference to FIG. 8A, as seen above, the adjustments toarrive at the given proxy levels are based on the statistical dataassociated with the average normal hearer (i.e., curve 412). That is,all of the adjustments presented in FIG. 8A are based on moving theperceived loudness to as close to a normalized loudness as possible.That said, in an alternative embodiment, the adjustments to arrive atthe given proxy levels can be based on the statistical data associatedwith the 95 percentile confidence interval (e.g., the area between (andon) curves 414 and 416). In this regard, by way of example only and notby way of limitation, in such an exemplary embodiment, no adjustmentwould be made with respect to the presentation levels between andincluding 45 dBHL and 60 dBHL, adjustments with respect to thepresentation levels below that range could entail adjustments based onthe curve 414, and adjustments with respect to the presentation levelsabove that range could entail adjustments based on the curve 416. Thatis, in an exemplary embodiment, the adjustments would be made to simplyobtain the proxy levels that fall within the 95^(th) percentileconfidence interval. That said, in an alternate embodiment, noadjustments would be made with respect the presentation levels betweenand including 45 dBHL and 60 dBHL, while adjustments outside of thatrange could entail adjustments based on the curve 412. That is, in anexemplary embodiment, the adjustments would be made sparingly, but ifthe adjustments were made, the adjustments would be to drive theresulting loudness to that which corresponds to as close to a normalizedloudness as possible. Still further, in at least some exemplaryembodiments, presentation levels below the range might be adjusted onlyto the curve 414, while presentation levels above the range might beadjusted only to the curve 412. Still further, in at least someexemplary embodiments, presentation levels below the range might beadjusted only to the curve 412, while presentation levels above therange might be adjusted only to the curve 416. Other variations arepossible in at least some embodiments. Any regime of adjustment based onthe statistical data for a normal hearer, whatever the range (50^(th)percentile, 40 to 60 percentile, etc.), can be utilized in at least someembodiments, providing that such has utilitarian value.

Still further, in at least some exemplary embodiments, the resultingproxy levels for values below and/or above a given range can be set suchthat changes are more gradual than that which would otherwise be thecase. By way of example only and not by way of limitation, the firstchange (e.g., 30 dB HL) can result in a proxy level based on the 95percentile confidence level (i.e., along curve 414), the second change(e.g., 35 dBHL) can result in a proxy level based on a pseudo-curve islocated between the floor of the 95 percentile confidence level and theaverage (i.e., between curve 414 and curve 412, such as by way ofexample only and not by way of limitation, ⅓rd of the way between thosetwo curves), the third change (e.g., 40 dBHL) can result in a proxylevel based on a pseudo-curve is located between the floor of the 95percentile confidence level and the average (i.e., between curve 414 andcurve 412, such as by way of example only and not by way of limitation,⅔rds of the way between those two curves), etc. Alternatively and/or inaddition to this, a similar but opposite concept can be utilized for thelouder values. Alternatively and/or in addition to this,empirically-based step size parameters can be applied so as to smooththe transition between the presentation levels resulting from theadjustments detailed herein. Any algorithm regime that will enable themap changes to be more gradual than that which would be the case, thatalso have utilitarian value, can in at least some embodiments beutilized.

Still further, it is noted that adjustments to the map changes can bemade based on features that are different than those associated withobtaining a gradual increase and/or decrease between presentationlevels. By way of example only and not by way of limitation, there maybe utilitarian value with respect to providing a limit on upward mapadjustments to within a certain safety net. For example, a maximal 10%upward increase might be applied as a limit to ensure that the resultingloudness is not too loud or otherwise results in a safety issue.

FIG. 8B presents an exemplary proxy gain adjustment curve reflecting howthe respective presentations levels would be adjusted based on methodaction 710 to obtain the proxy loudness levels (i.e., the vertical datapoints on the curve of FIG. 9 correspond to the horizontal arrows ofFIG. 8 and the horizontal data points on the curve of FIG. 9 correspondto the respective bases of those arrows).

With reference back to FIG. 7, after method action 710, method action720 is executed, which entails replacing the respective current levelsapplied at the respective presentation levels by an amount correlated tothe offset data obtained in action 710. In an exemplary embodiment,method action 720 is executed to develop the electrical output functionthat will result in a hearing percept that is perceived by the recipientis having a loudness that is at least closer to that of a normal hearingperson for a given stimuli.

An exemplary method of executing method action 720 will now bedescribed, based on a scaling test for sounds at 250 Hz, where therecipient-specific loudness data and the statistical loudness data hasalready been obtained. In this regard, FIG. 9A presents a chartdetailing the scaling test results for various presentation levels, andthe normal hearing statistical data for those same presentation levels(curves 910 and 920, respectively), and FIG. 9B presents a chartdetailing the difference between the scaling test results and the normalhearing statistical data for those same presentation levels, where alinear curve fit has been applied for both figures. The curve 910 ofFIG. 9A has an average loudness scaling error (LS) of 0.91, relative tothe statistical curve 920, averaged over the presentation levels. It isfurther noted that in an exemplary embodiment, the action of obtainingthe recipient specific loudness data further includes the action ofobtaining the current regime hearing prosthesis to evoke the hearingpercepts associated therewith (e.g., the embryonic map used by thehearing prosthesis to evoke the hearing percepts utilized to develop thescaling test data). FIG. 9C presents that current regime (curve 930). Inthis regard, the electrode corresponding to the test frequency isdetermined or otherwise known (hence the current regime for thatelectrode can be determined). By way of example only, for this testfrequency of 250 Hz, utilizing, by way of example, the standardfrequency allocation table (or a customized frequency allocation tableas the case may be) of a fully functioning 22 contact electrode array ofa cochlear implant, the electrodes having a center frequencycorresponding best to (e.g., closest to) the tested frequency isidentified. It is noted that this can be generalized to other frequencyallocation tables, such as by way of example only and not by way oflimitation, in the case that some electrodes are disabled for whateverreason. It is further noted that in an exemplary embodiment, the testfrequencies can be customized to correspond to a given electrode of theelectrode array. That is, empirical data can be utilized to determinethe frequency of a given electrode (e.g., electrode X corresponds to 273Hz), and the tone can be customized to that specific frequency (e.g., to273 Hz), instead of having to simply use the best (closest) electrode toa test frequency. That said, such might not necessarily be feasible inscenarios where the statistical data is provided for a given specificfrequency. That said, in at least some embodiments, some methods entailadjusting the statistical data for one frequency that it is applicablefor another frequency. This can be achieved via the utilization of otherstatistical data that enables such adjustment. Any device, system,and/or method that will enable the correlation between test frequencyand a given electrode can be utilized in at least some embodiments.

In an exemplary embodiment, to replace the respective current levelapplied at the respective presentation levels by an amount correlated tothe offset data obtained in action 710, using the obtained current data(e.g., the data represented by curve 930), for each presentation level,the adjustment gain is added to the level in the electrical output isdetermined for that new game based on the adjustment gain. With respectto FIG. 9C, for the loudness level of 30 dBSPL, the adjustment gain is11 dB, which results in a proxy loudness level of 41 dBSPL. Thecorresponding current for that electrode corresponds to approximately 7nC (as opposed to approximately 6 nC for the current utilized at theloudness level for the scaling test). This is represented by theleftmost “+” symbol. This is now the new current level for the newcurrent regime (the new map) for sounds having a loudness of 30 dBSPL.Again, this process is repeated for each loudness level (35 dBSPL, 40dBSPL, 45 dBSPL, etc.), although in some alternate embodiments, not allloudness levels are used. The resulting new current levels can be seenby the various “+” symbols on FIG. 9C, where a curve 940 has beensuperimposed thereon using a curve fitting technique. In this regard, anexemplary embodiment entails utilizing a data manipulation technique,such as by way of example only and not by way of limitation, a curvefitting technique (e.g., linear fitting), to find the optimal thresholdlevel and comfort levels that approximate resulting values, the resultbeing that curves 940 are bounded by new threshold levels and comfortlevels. As can be seen, the general trend is that for sounds having aloudness below about 57 dBSPL, the current levels are increase relativeto those utilized in the scaling test (those of the first regime), andfor sounds having a loudness above about 55 dBSPL, the current levelsare decreased relative to those utilized in the scaling test (those ofthe first regime). Utilizing this new electrical current data, a newcurrent regime (new map) is developed, as represented by curve 950 inFIG. 9D (which also shows curve 930, representing the previous currentregime (embryonic map). As can be seen, the portions of the currentregime below the loudness levels of the scaling test have beenextrapolated utilizing data other than the data associated with theloudness test, and the portions of the current regime above the loudnesslevels of the scaling test have been truncated at a constant currentlevel. In an exemplary embodiment, these portions of the current regimeare developed utilizing standard fitting methods are developed utilizingstandard fitting protocols according to accepted guidelines. By way ofexample only and not by way of limitation, the current regime of FIG. 9Dwas developed utilizing a linear alpha model having two degrees offreedom (a threshold value in a comfort value), without limiting at highloudness values and clipping low loudness values.

From FIGS. 9C and 9D, it can be seen that the threshold levels and thecomfort levels (T and C levels, respectively) of the two differentcurrent regimes are different. Specifically, in the embodiments of FIGS.9C and 9D, the range between the threshold level and the comfort levelis compressed for the new current regime relative to the old currentregime. More specifically, FIG. 9C presents a threshold level of 140(where 140 is a genericized value, as opposed to a nanoCoulomb value)and a comfort level of 170 (again where 170 is a generic sized value).In view current regime, the new threshold level is now 150 and the newcomfort level is now 168 (again generic sized values).

In an exemplary embodiment, these new current regimes result in ahearing percept having a normalized loudness, or at least closer to anormalized loudness, with respect to a normal hearing person. That is,in an exemplary embodiment, the electrical stimulation level that isdelivered for a given stimulus of a given loudness is that whichcorresponds to another electrical level (or an extrapolated electricallevel associated therewith, more on this below), utilized in anotherpresentation level of the scaling test), where the another electricallevel resulted in a hearing percept having a loudness closer to(including the same as), the loudness of a normal hearing person.

It is noted that in an exemplary embodiment, the scaling test providedincludes providing sounds having different frequencies. That is, theresults of FIGS. 4 and 8A will be present for different frequencies. Byway of example only and not by way of limitation, in an exemplaryembodiment, a scaling test can encompass 3 different frequencies, suchas by way of example only and not by way of limitation, 250 Hz, 1000 Hzand 4000 Hz. The above manipulation steps detailed can be also appliedto these different frequencies. In this regard, FIGS. 10A-10D correspondrespectively to FIGS. 9A-9D, except for a test frequency of 1000 Hz.Still further in this regard, FIGS. 11A-11D correspond respectively toFIGS. 9A-9D, except for a test frequency of 4000 Hz. As can be seen, inthese exemplary examples, the trend is generally the same: a perceptionof loudness levels lower than the statistical norm at the softer levels,a perception of loudness levels higher than the statistical norm atlouder levels, and a shrinking of the threshold levels and the comfortlevels at both ends of the loudness spectrum resulting from the newelectrical regime (new map), with the most pronounced changes resultingin the low end of the loudness spectrum. That said, these are onlyexemplary examples. In alternative embodiments, the results could bedifferent. By way of example only and not by way of limitation, theresults could be reversed, where the perception of loudness levels forsofter levels are higher than the statistical norm, and the perceptionof loudness levels at the louder levels are lower than the statisticalnorm and/or the threshold levels and comfort levels could be expanded atboth ends, or variations thereof (e.g., the threshold level could beraised at one end and also raised at another end and/or vice versa, theadjustment could result in increased current levels across all of theloudness levels or a decrease in the current levels across all of theloudness levels, an increase in the loudness levels with a decrease inthe middle the loudness levels or vice versa etc.).

The above presents some high-level algorithmic details of someembodiments at the macro level. Now, some specific algorithm detailswill be provided at the micro level. Again, to be clear, all data hereinis exemplary, despite the fact that the data is often taken to thefourth decimal place.

The below chart presents a matrix of data associated with exemplarypresentation levels of an exemplary scaling test using a sound at 250Hz, where the columns correspond to the respective presentation levels,and the rows correspond to the loudness level for the given presentationlevel, the proxy level based on the normal hearing statistical data forthe given presentation level, the adjustment to the loudness level toreach the proxy level based on the normal hearing statistical data andthe current levels in nanoColoumbs used for each presentation level.

30 35 40 45 50 55 60 65 41 42.5 44 45 52.996 55 57 62 11 7.5 4 0 2.996 0−3 −3 5.9725 6.4719 6.9713 7.4707 7.9701 8.4695 8.9689 9.4683

An exemplary algorithm entails using the above data to obtain newcurrent levels that will be used in a new map. By way of example, foreach presentation level (stimulus), or a subset thereof, the currentlevels associated with the actual loudness levels are utilized for theproxy levels that correspond to the actual loudness levels. For example,with respect to the presentation level of 30 dBHL, the proxy leveldetermined based on the statistical data corresponds to 41 dBHL. Thecurrent levels associated with the actual loudness level for 41 dBHL arenot explicitly known, but the current level for the loudness level of 40dBHL and the current level for the loudness level of 45 dBHL are known,and these are 6.9713 nC and 7.4707 nC, respectively (i.e., these are thecurrent levels that are utilized to evoke a hearing percept to developthe recipient-specific data from the scaling test). Via linearinterpolation (in alternate embodiments, other methods can be used), acurrent level value is developed for the proxy level of 41 dBHL, whichcorresponds to 7.07118 nC. This becomes the new current level for thenew map for sounds having a loudness of 30 dBHL. Because this currentlevel evokes a hearing percept that is perceived to have a loudnesscloser to that which would be perceived by the average normal hearingperson than that of the old current level (5.9725 nC), the map willprovide a more normalized perception of loudness for that specificrecipient. This process is repeated for all of the presentation levels,resulting in the following, where the rows correspond to the loudnesslevel for the given presentation level (which will correspond to afuture stimuli loudness at which the hearing prosthesis will respondusing the new current levels), the proxy level based on the normalhearing statistical data for the given presentation level, theadjustment to the current level to reach the new current level that willevoke a hearing percept that is perceived as being as loud as thatperceived by a normal hearing person for that loudness level, and thecurrent levels in nanoCoulombs to be used in the new map when a stimulushaving a loudness at the presentation level is applied to the hearingprosthesis in the future (for the electrode corresponding to 250 Hz).

30 35 40 45 50 55 60 65 41 42.5 44 45 52.996 55 57 62 0.09988 0.24970.39952 0 0.29924 0 −0.29964 −0.29964 7.07118 7.221 7.37082 7.47078.26934 8.4695 8.66926 9.16866

Accordingly, in an exemplary embodiment, during future use of thehearing prosthesis utilizing the new map, when a sound is capturedhaving a loudness level of, for example, 35 dB at a frequency of 250 Hz,the current applied to the pertinent electrode will be 7.221 nC, andwhen a sound is captured having a loudness level of, for example, 55 dB,at that same frequency, the current applied to the pertinent electrodewill be 8.4695 dB. (Note that these values are values where a linearcurve fitting is applied to develop a new current regime utilizing thedata above. Other data manipulation methods may result in differentcurrent values due to the fact that the data manipulation (e.g. curvefitting techniques) might not necessarily drive the curve through eachdata point.)

The below chart presents a matrix of data associated with exemplarypresentation levels of an exemplary scaling test using a sound at 1000Hz, where the columns correspond to the respective presentation levels,and the rows correspond to the loudness level for the given presentationlevel, the proxy level based on the normal hearing statistical data forthe given presentation level, the adjustment to the loudness level toreach the proxy level based on the normal hearing statistical data andthe current levels in nanoCoulombs used for each presentation level.

30 35 40 45 50 55 60 65 39 40 48 45 56 57 58.5 59.5 9 5 8 5 5.996 1.997−1.5015 −5.5005 5.9534 6.4927 7.0319 7.5712 8.1105 8.6498 9.189 9.7283

The above process is repeated for all of the presentation levels,resulting in the following, where the rows correspond to the loudnesslevel for the given presentation level, the proxy level based on thenormal hearing statistical data for the given presentation level, theadjustment to the current level to reach the new current level that willevoke a hearing percept that is perceived as being as loud as thatperceived by a normal hearing person for that loudness level, and thecurrent levels in nanoCoulombs to be used in the new map (for theelectrode corresponding to 250 Hz).

30 35 40 45 50 55 60 65 39 40 47.996 45 55.996 56.997 58.4985 59.49950.43136 0.5392 0.862449 0.5393 0.646729 0.215356 −0.16192 −0.593286.92406 7.0319 7.894349 8.1105 8.757229 8.865156 9.027078 9.135016

The below chart presents a matrix of data associated with exemplarypresentation levels of an exemplary scaling test using a sound at 4000Hz, where the columns correspond to the respective presentation levels,and the rows correspond to the loudness level for the given presentationlevel, the proxy level based on the normal hearing statistical data forthe given presentation level, the adjustment to the loudness level toreach the proxy level based on the normal hearing statistical data andthe current levels in nanoCoulombs used for each presentation level.

30 35 40 45 50 55 60 65 39 40 40 43 45 46 47 48 5.9248 6.5323 7.13997.7474 8.3549 8.9625 9.57 10.1776 7.0183 7.1399 7.1399 7.5044 7.74747.8689 7.9904 8.1119

The above process is repeated for all of the presentation levels,resulting in the following, where the rows correspond to the loudnesslevel for the given presentation level, the proxy level based on thenormal hearing statistical data for the given presentation level, theadjustment to the current level to reach the new current level that willevoke a hearing percept that is perceived as being as loud as thatperceived by a normal hearing person for that loudness level, and thecurrent levels in nanoCoulombs to be used in the new map (for theelectrode corresponding to 250 Hz).

30 35 40 45 50 55 60 65 39 40 40 45 45 46 47 48 0.48608 0.6076 0 −0.243−0.6075 −1.09368 −1.5795 −2.06584 7.01838 7.1399 7.1399 7.5044 7.74747.86882 7.9905 8.11176

Accordingly, in view of the above, the algorithms detailed up to nowhave enabled the development of data having utilitarian value tonormalize loudness hearing percepts relative to a normal hearing personfor specific frequencies (the frequencies of the scaling test).

In view of the above, with reference back to the method of flowchart 600of FIG. 6, in an exemplary embodiment, the action of adjusting at leastone of the respective current levels entails increasing the at least oneof the respective current levels to an amount that is at least proximate(which includes the same as) the another current level (e.g., as isconceptually represented by the resulting curve 950 relative to thecurve 930 of FIGS. 9D, 10D and 11D). As used herein, the phrase“proximate another current level” includes any current level thatresults in a perceived loudness that is closer to a normalized loudnessthan that which would be the case without the teachings detailed herein.Also, as will be understood from the above, the action of adjusting atleast one of the respective current levels can entail increasing the atleast one of the respective current levels to an amount that is at leastone of at or is an extrapolated value from the another current level(e.g., resulting in the lower loudness level portions of the curve 950relative to the curve 930).

In an exemplary embodiment, the action of creating the map for thehearing prosthesis entails creating the map based on the obtained databy adjusting at least one other of the respective current levels basedon data of a respective perceived loudness for another current leveldifferent from that upon which the at least one of the respectivecurrent levels was adjusted. An exemplary method further includesadjusting the at least one other of the respective current levels bydecreasing the at least one other of the respective current levels to anamount that is at least one of at or is an extrapolated value from theanother current level different from that upon which the at least one ofthe respective current levels was adjusted (e.g., resulting in thehigher loudness level portions of the curve 950 relative to the curve930).

Still further, in view of the above, again with continuing reference tothe method associated with FIG. 6, the action of adjusting at least oneof the respective current levels entails identifying a respectiveperceived loudness for the another current level based on a correlationwith the statistical data. This is generally represented conceptually byFIG. 8A in combination with FIGS. 9D, 10D and 11D.

Corollary to the above is that in at least some exemplary embodiments,the different current levels of the plurality of hearing percepts arecorrelated to respective different loudness levels of respectivedifferent noise stimuli, wherein higher loudness level is directlycorrelated with higher current level. This is seen in FIGS. 9C, 10C, and11C. Still further, the action of adjusting at least one of therespective current levels entails identifying the respective perceivedloudness for the another current level that corresponds to a normalizedloudness for the respective different noise stimulus and using theanother current level to develop adjustment data to adjust the at leastone of the respective current levels. This is generally conceptuallyrepresented by FIG. 8A in combination with FIGS. 9B, 9C, 10B, 10C, 11Band 11C.

Some exemplary embodiments further include methods of developing thedifferent current regimes to normalize loudness for frequenciesdifferent than those utilized in the scaling test. That is, in anexemplary embodiment, not all frequencies will be utilized as testfrequencies in the loudness scaling test. Thus, in an exemplaryembodiment, to complete a map adjustment for monopolar maps,interpolation can be utilized. In this regard, in an exemplaryembodiment, utilizing the three test frequencies and the map adjustmentsdeveloped above (where, in some exemplary embodiments, data manipulationtechniques, such as curve fitting techniques, are applied to develop aregime that addresses not only loudness levels corresponding to thespecific presentation levels, but also to the levels in between), theother electric parameters can be linearly interpolated. In this regard,FIG. 12 depicts a series of curves presenting genericized current levelsrelative to electrode number for the original map (original currentregime) utilized to evoke a hearing percepts in the scaling test (thedotted solid lines), with the electrode numbers corresponding to thoserelated to the frequencies of the three frequency tests administeredabove encased in the 3 respective boxes (electrode 1 corresponding to250 Hz, electrode 7 corresponding to 1000 Hz, and electrode 17corresponding to 4000 Hz). The top two curves correspond to comfortlevel curves and the bottom two curves correspond to threshold levelcurves.

In at least some exemplary embodiments, the current level value for eachof the electrodes for the original current level regime (the originalmap) utilized to evoke a hearing percept during scaling test is known.In this regard, each dot represents the exact portion of the maputilized during the scaling test. Superimposed onto FIG. 12 are thecurrent levels corresponding to the adjusted current levels resultingfrom the above algorithms. These are located within the boxes encasingelectrodes 1, 7, and 17, represented by the “+” symbol. In the exemplaryembodiment presented in FIG. 12, linear interpolation has been utilizedto develop data for each of the electrodes in between the electrodescorresponding to the frequencies utilized during the scaling test.Again, in some other embodiments, other types of data manipulation/datamanagement can be utilized. That is, linear interpolation is one of thevarious ways to develop the data for the non-presentation frequencies.

In at least some exemplary embodiments, for frequencies above highestfrequencies utilized during the scaling test (e.g., 4000 Hz), theadjustment for the highest frequency (e.g., 4000 Hz) is utilized. Thatsaid, in an alternate embodiment, the values can be extrapolated usingany applicable data manipulation technique that can have utilitarianvalue (e.g., linear extrapolation).

Accordingly, in an exemplary embodiment, a new map can be developedhaving threshold levels and comfort levels corresponding to those of anormal hearing person for a given set of stimuli. In some exemplaryembodiments, standard electrical output functions of known utilitarianvalue can be utilized to develop the current regime between thethreshold levels and comfort levels, at least for the electrodes otherthan those utilized for the scaling test (although, in an alternateembodiment, the empirical data for those tests can also be substitutedby these standard electrical output function for consistency). By way ofexample only and not by way of limitation, FIG. 13 presents an exemplaryfunction that can be used to fill in the data in between the thresholdlevel (TSPL) and the comfort level (CSPL). That is, the current levelfor the threshold level and the current level for the comfort level inthe superimposed onto the graph of FIG. 13 at the T position and the Cposition, respectively, and the current levels for loudness is therebetween can be developed following the curve between those twopositions.

In an alternate embodiment, the current regime for the non-testelectrodes for loudness levels in between the threshold level and/orcomfort level can be developed utilizing data manipulation based on theempirical results from those loudness levels from the scaling test.Again, in at least some exemplary embodiments, linear interpolation canbe utilized from the empirical test results for those in betweenloudness levels for the known test electrodes to develop current regimesfor the non-test electrodes.

Accordingly, in at least some exemplary embodiments detailed herein, anew map can be developed that better approximates normal hearingloudness. This new electrical map can then be approximated within theparameters space of the exposed clinical parameters. In at least someexemplary embodiments of the algorithms detailed herein, the algorithmresults in a proportional relationship between the parameters. Forexample, small deviations from the normal hearing regime will result insmall map changes, while large deviations from the normal hearing regimewill result in large map changes, at least in some exemplaryembodiments.

Now, with reference to FIG. 14, another exemplary method will bedescribed. FIG. 14 presents a flowchart 1400, which includes methodaction 1410, which entails obtaining data indicative of respectiveperceived loudness levels for a plurality of hearing perceptsrespectively evoked based on respective different stimulus havingrespective first different loudness levels, wherein the respectiveevoked hearing percepts are evoked with respective different energyoutputs of a hearing prosthesis. This is conceptually represented bycurve 410 of FIG. 4, curve 910 of FIG. 9A, and curve 930 of FIG. 9C.Flowchart 1400 further includes method action 1420, which entailsobtaining data indicative of normalized loudness levels for normalhearers for the respective different stimulus having respectivedifferent first loudness levels. This is represented by curve 412 ofFIG. 4 and curve 920 of FIG. 9A.

Flowchart 1400 further includes method action 1430, which entailsconfiguring the hearing prosthesis to automatically evoke hearingpercepts, in response to sound captured by the hearing prosthesis havingrespective second different loudness levels corresponding to therespective first different loudness levels, at respective new differentenergy levels different from those used to evoke the respective hearingpercepts, for respective new respective stimulus having the respectivefirst different loudness levels, based on the obtained data indicativeof normalized loudness levels. This is conceptually represented byloading a map into the hearing prosthesis having an electrical currentregime based on curves 950 of FIGS. 9D, 10D and 11D. In a similar vein,in an exemplary embodiment, the action of configuring the hearingprosthesis entails setting a map of the hearing prosthesis toautomatically evoke the hearing percepts at respective energy levels inresponse to sound captured by the hearing prosthesis having, relative tothe respective current levels, respective loudness levels correspondingto those of the respective different stimulus based on the obtaineddata.

In at least some exemplary embodiments, the action of obtaining dataindicative of respective perceived loudness levels entails obtainingempirical perceived loudness data for a plurality of differentpresentation levels of a loudness test administered to a recipient ofthe hearing prosthesis. This is conceptually represented by FIGS. 4 and8 as detailed above.

In an exemplary embodiment of the method represented by FIG. 14, thereis a variation of that method which entails developing (which includessimply obtaining from another source) a first current level regime inwhich respective loudness levels of the respective different stimulusare correlated with respective current levels of an electrode array ofthe hearing prosthesis. This is conceptually represented by obtainingthe curves 930 of FIGS. 9C, 10C and 11C. This variation of the methodcan further entail developing a second current level regime in whichrespective loudness levels of future sounds captured by the hearingprosthesis are correlated with respective future current levels of theelectrode array. This is conceptually represented by obtaining thecurves 950 of FIGS. 9D, 10D and 11D. This variation of the method canfurther result in the action of configuring the hearing prosthesis toautomatically evoke hearing percepts at respective energy levels suchthat the hearing prosthesis is configured to automatically evoke hearingpercepts according to the second current level regime instead of thefirst current level regime. Again, in an exemplary embodiment, such canbe achieved by developing a map based on the curves 950 of FIGS. 9D, 10Dand 11D, and loading that map into the hearing prosthesis such that thehearing prosthesis will evoke a hearing percept based on that map.

Corollary to the above is that, in at least some exemplary embodiments,the action of developing the second current regime entails adjusting therespective current levels of the first regime to those of the secondregime for respective loudness levels of the different stimulus andfuture sounds that are the same, based on values of the current level ofthe first regime and the obtained data indicative of normalized loudnesslevels for normal hearers, wherein the obtained data indicative ofnormalized loudness levels is statistical data. This is conceptuallyrepresented by FIGS. 9C, 10C and 11C and FIGS. 9D, 10D and 11D.

Along these lines, in an exemplary embodiment of the method of FIG. 14,the method results in a scenario where the action of configuring thehearing prosthesis results in the hearing prosthesis automaticallyevoking hearing percepts that have loudness percepts closer to those ofthe normalized loudness levels for the respective different stimulusrelative to that which is the case for the obtained data indicative ofthe respective perceived loudness levels. This is conceptuallyrepresented by FIG. 8A above.

With reference back to FIG. 12, it can be understood that in at leastsome exemplary embodiments, the method of FIG. 14 can further compriseobtaining second data indicative of respective perceived loudness levelsfor a plurality of hearing percepts respectively evoked based onrespective different stimulus at a second frequency having respectivefirst different loudness levels, wherein the respective evoked hearingpercepts are evoked with the respective different energy outputs of ahearing prosthesis. This is conceptually represented by curve 910 ofFIG. 10A (or 11A), and curve 930 of FIG. 10C (or 11C). An exemplarymethod can further entail obtaining second data indicative of normalizedloudness levels for normal hearers for the respective different stimulusat the second frequency having the respective different first loudnesslevels. This is conceptually represented by curve 920 of FIG. 10A (or11A). The currently discussed exemplary method can further entailconfiguring the hearing prosthesis to automatically evoke hearingpercepts, in response to sound at the second frequency captured by thehearing prosthesis having the respective second different loudnesslevels corresponding to the respective first different loudness levels,at respective new second different energy levels different from thoseused to evoke the respective hearing percepts based on respectivedifferent stimulus at the second frequency, for respective newrespective stimulus having the respective first different loudnesslevels and the second frequency, based on the obtained data indicativeof normalized loudness levels for the second frequency. This isconceptually represented by following the procedure detailed above withrespect to FIG. 12 to develop a map based on the electrical currentregimes based on curves 950 of FIGS. 10D in combination with data basedon curves 950 of FIGS. 9D, and/or 11D. As will be readily apparent fromthe teachings detailed above, in at least some examples of thisexemplary method, at least some of the respective new different energylevels will be different than at least some of the respective second newdifferent energy levels for respective first different loudness levels.

The teachings detailed herein and/or variations thereof are applicableto both cochlear implants, and other types of hearing prostheses thatutilize a gain function. In this regard, by way of example, not only arethe teachings detailed herein applicable to a cochlear implant, in atleast some embodiments, the teachings detailed herein are applicable toa bone conduction device and/or a middle ear implant. Still further, theadjusted values detailed herein can be applied directly in the acousticchannels of a hybrid device and/or a wide dynamic range compressionhearing aid. Accordingly, in an exemplary embodiment, there is a methodof fitting such devices utilizing one or more or all of the methodactions detailed herein. Still further, in an exemplary embodiment,there are such devices fitted to a recipient by executing one or more orall the method actions detailed herein.

In general terms, an exemplary embodiment entails the development of amap that results in the control of the amplification (e.g., gain) of thehearing prosthesis (or some other parameter and/or parameters) thatresults in a hearing percept such that the resulting hearing percept fora given stimulus and/or for a range of stimuli has a perceived loudnessthat is at least similar to (or at least closer to), if not identicalto, a loudness perceived for the given stimulus/range of stimuli by anormal hearing person. Also in general terms, the developed map canresult in the control of one or more various parameters that in turnresults in a hearing percept, wherein the resulting hearing percept fora given stimulus and/or for a range of stimuli has a perceived loudnessthat is at least closer to a loudness perceived for the givenstimuli/range of stimulus by a normal hearing person relative to thatwhich is (was) the case without the control.

In general terms, in an exemplary embodiment, there is a method of usinga three-step algorithm (no additional steps are needed in someembodiment) to tune map parameters of a frequency channel. Loudnessratings resulting from the hearing prosthesis recipient based on hearingpercepts utilizing an initial map can be utilized to generate a new map.In at least some embodiments, a model of the electrical output functionof a given hearing prosthesis as initially set is utilized to develop aninitial dataset relating to perceived loudness, and this initial datasetis utilized to develop a new electrical output function by comparing thedata set to statistical values relating to loudness. An exemplary methodestimates adjustment gains that can be utilitarianly made to adjust themap such that the adjusted map (new map) results in the hearing percepthaving loudness values more closely approximating (if not generallyidentical to) a normal hearing person.

Moreover, an exemplary embodiment entails utilizing the same approachesas detailed herein (e.g., the same algorithms detailed herein), tonormalize both electrical hearing and acoustical hearing parameters.Accordingly, an exemplary embodiment entails fitting an electricalhearing device and an acoustic hearing device utilizing the samealgorithm according to the teachings detailed herein, at least tonormalize loudness. Again, this can be applicable to a hybrid system(where the cochlear implant and acoustical device are utilized in thesame ear) or a contralateral system (a bimodal system, where one sideutilizes an electrical hearing device and the other utilizes anothertype of hearing device, such as an acoustic hearing device).Accordingly, an exemplary embodiment entails utilizing the sameapproaches as detailed herein (e.g., the same algorithms detailedherein) to normalize the hearing parameters of both of the components ofa hybrid system and/or a contralateral system. Accordingly, an exemplaryembodiment entails fitting a hybrid system and/or a contralateral systemutilizing the same algorithm according to the teachings detailed herein,at least to normalize loudness.

In keeping with the above, in an exemplary embodiment, the methodsdetailed herein can be utilized to instead develop a compression regimeadjustment regime of a hearing prosthesis. That is, in an exemplaryembodiment, the map of the hearing prosthesis is not necessarily changed(e.g., the map utilized to implement the scaling test is not changed/thehearing prosthesis maintains that map after the methods detailed hereinare implemented). Instead, a block is built into the hearing prosthesisthat gives varying additional amplification per channel that iscorrelated to the loudness of various sound captured by the hearingprosthesis. Any device, system, and/or method that can implement theteachings detailed herein, such that the resulting hearing percept isnormalized, can be utilized in at least some embodiments.

It is noted that while the teachings detailed herein are described interms of an electrical stimulating device in the form of a cochlearimplant, it is noted that alternate embodiments are applicable to othertypes of stimulating devices. By way of example only and not by way oflimitation, the teachings detailed herein and/or variations thereof canbe applicable to a bone conduction device, a Direct Acoustic CochlearImplant, or traditional hearing aids, at least those having channelfeatures. Indeed, in the embodiments where there are no specificallydivided channels, proxy channels can be established. That is, thefrequency spectrum can be divided into frequency bands for datamanipulation purposes, and the respective frequency bands can be treatedas channel.

As noted above, at least some of the method actions can be executed at alocation remote from where another method action is located. Forexample, it is noted that an exemplary embodiment entails executing someor all of the method actions detailed herein, where the recipient of thehearing prosthesis is located remotely (e.g., geographically distant)from where at least some of the method actions detailed herein areexecuted (e.g., any method action detailed herein that can be executedby, for example, a computer or other processor located at a remotelocation). For example, any of the methods detailed herein could beexecuted via internet communication with the hearing prosthesis and theuser interface 314 and/or the hearing implant fitting system 306 (e.g.,communication link 308 of FIG. 3 can be an internet connection or awired or wireless connection). Still further by example, with respect toa given method, one or more method actions can be executed at onelocation (controlled by the audiologist 304 at another locationgeographically remote from the one location), and one or more othermethod actions can be executed at the location where the audiologist 304is located. That is, any method action herein can be executed at onelocation, and any method action herein can be executed at anotherlocation, and so on, providing that the teachings detailed herein and/orvariations thereof can be practiced.

It is further noted that in an alternate embodiment, one or more of themethod actions detailed herein are executed by the recipient of thecochlear implant. Indeed, in an exemplary embodiment, there is a systemthat enables a recipient to execute, in conjunction with the system, themethod actions detailed herein such that the cochlear implant can beremapped without any additional input from a clinician or the like.

It is noted that any disclosure of a method action detailed hereincorresponds to a disclosure of a corresponding system and/or device forexecuting that method action, in at least some embodiments,automatically. It is further noted that any disclosure of an apparatusor system herein corresponds to a disclosure of a method of operatingthat apparatus. It is also noted that any disclosure of any methodaction detailed herein further includes a disclosure of executing thatmethod action in an automated fashion, as well as a device for executingthose method actions in the automated manner.

It is further noted that any disclosure of a fitting method hereincorresponds to a hearing prosthesis or hearing device fitted accordingto that method.

While various embodiments of the present invention have been describedabove, it should be understood that they have been presented by way ofexample only, and not limitation. It will be apparent to persons skilledin the relevant art that various changes in form and detail can be madetherein without departing from the scope of the invention.

What is claimed is:
 1. A method, comprising: obtaining data indicativeof respective perceived loudness levels for a plurality of hearingpercepts respectively evoked at different current levels; creating a mapfor a hearing prosthesis based on the obtained data by adjusting atleast one of the respective current levels of the different currentlevels based on data of a respective perceived loudness for anothercurrent level; and configuring the hearing prosthesis to have thecreated map.
 2. The method of claim 1, wherein: the action of adjustingat least one of the respective current levels includes increasing the atleast one of the respective current levels to an amount that is at leastproximate to another current level.
 3. The method of claim 1, wherein:the action of adjusting at least one of the respective current levelsincludes increasing the at least one of the respective current levels toan amount that is at least one of at the another current level or at anextrapolated value from the another current level.
 4. The method ofclaim 3, further comprising: creating the map for the hearing prosthesisbased on the obtained data by adjusting at least one other of therespective current levels based on data of a respective perceivedloudness for another current level different from that upon which the atleast one of the respective current levels was adjusted; and adjustingthe least one other of the respective current levels by decreasing theat least one other of the respective current levels to an amount that isat least one of at or is an extrapolated value from the another currentlevel different from that upon which the at least one of the respectivecurrent levels was adjusted.
 5. The method of claim 1, wherein: theaction of adjusting at least one of the respective current levelsincludes adjusting the at least one of the respective current levelsbased on statistical data; the action of adjusting at least one of therespective current levels includes identifying a respective perceivedloudness for the another current level based on a correlation with thestatistical data.
 6. The method of claim 1, wherein: the differentcurrent levels of the plurality of hearing percepts are correlated torespective different loudness levels of respective different noisestimulus, wherein higher loudness level is directly correlated withhigher current level, and the action of adjusting at least one of therespective current levels includes identifying the respective perceivedloudness for the another current level that corresponds to a normalizedloudness for the respective different noise stimulus and using theanother current level to develop adjustment data to adjust the at leastone of the respective current levels.
 7. A method, comprising: obtainingdata indicative of respective perceived loudness levels for a pluralityof hearing percepts respectively evoked based on respective differentstimulus having respective first different loudness levels, wherein therespective different stimulus are correlated with respective currentlevels of an electrode array of the hearing prosthesis, and wherein therespective evoked hearing percepts are evoked with respective differentenergy outputs of a hearing prosthesis; obtaining data indicative ofnormalized loudness levels for normal hearers for the respectivedifferent stimulus having respective different first loudness levels;and subsequent to the action of obtaining data indicative of respectiveperceived loudness levels, configuring the hearing prosthesis toautomatically evoke hearing percepts at respective new different energylevels different from those previously used to evoke the previousrespective hearing percepts when sound is subsequently captured by thehearing prosthesis having respective second different loudness levelscorresponding to the respective first different loudness levels, for newrespective stimulus having the respective first different loudnesslevels, based on the obtained data indicative of normalized loudnesslevels.
 8. The method of claim 7, wherein: the action of configuring thehearing prosthesis includes setting a map of the hearing prosthesis toautomatically evoke the hearing percepts at respective energy levels inresponse to sound captured by the hearing prosthesis having, relative torespective current levels, respective loudness levels corresponding tothose of the respective different stimulus based on the obtained data.9. The method of claim 7, further comprising: developing a first currentlevel regime in which respective loudness levels of the respectivedifferent stimulus are correlated with respective current levels of anelectrode array of the hearing prosthesis; and developing a secondcurrent level regime in which respective loudness levels of futuresounds captured by the hearing prosthesis are correlated with respectivefuture current levels of the electrode array, wherein the action ofconfiguring the hearing prosthesis to automatically evoke hearingpercepts at respective energy levels includes configuring the hearingprosthesis to automatically evoke hearing percepts according to thesecond current level regime instead of the first current level regime.10. The method of claim 9, wherein the action of developing the secondcurrent regime includes: adjusting the respective current levels of thefirst regime to those of the second regime for respective loudnesslevels of the different stimulus and future sounds that are the same,based on values of the current level of the first regime and theobtained data indicative of normalized loudness levels for normalhearers, wherein the obtained data indicative of normalized loudnesslevels is statistical data.
 11. The method of claim 9, furthercomprising: providing a recipient of the hearing prosthesis a loudnesstest wherein hearing percepts are evoked according to the first currentlevel regime; and using data pertaining to perceived loudness levels ofrespective stimulus provided during the loudness test to develop thesecond current level regime.
 12. The method of claim 7, furthercomprising: obtaining second data indicative of respective perceivedloudness levels for a plurality of hearing percepts respectively evokedbased on respective different stimulus at a second frequency havingrespective first different loudness levels, wherein the respectiveevoked hearing percepts are evoked with the respective different energyoutputs of a hearing prosthesis; obtaining second data indicative ofnormalized loudness levels for normal hearers for the respectivedifferent stimulus at the second frequency having the respectivedifferent first loudness levels; and configuring the hearing prosthesisto automatically evoke hearing percepts, in response to sound at thesecond frequency captured by the hearing prosthesis having therespective second different loudness levels corresponding to therespective first different loudness levels, at respective new seconddifferent energy levels different from those used to evoke therespective hearing percepts based on respective different stimulus atthe second frequency, for respective new respective stimulus having therespective first different loudness levels and the second frequency,based on the obtained data indicative of normalized loudness levels forthe second frequency.
 13. A fitting system, comprising: a sub-systemconfigured to obtain statistical perceived loudness data; a sub-systemconfigured to obtain hearing prosthesis recipient-specific loudness datafor a plurality of different stimulus having at least some loudnesslevels corresponding to those of the statistical perceived loudnessdata; and a sub-system configured to configure a hearing prosthesisbased on the obtained statistical data and the obtainedrecipient-specific loudness data, wherein the sub-system configured toconfigure the hearing prosthesis is configured to adjust at least onecurrent level setting of the hearing prosthesis by at least one of:increasing the at least one of the respective current level setting toan amount that is at least proximate to another current level; orincreasing the at least one of the respective current level setting toan amount that is at least one of at the another current level or at anextrapolated value from the another current level.
 14. The system ofclaim 13, wherein: the obtained recipient-specific loudness data isgenerated using the hearing prosthesis to evoke a plurality of hearingpercepts using a first map; the sub-system configured to automaticallydetermine respective offsets between the recipient-specific loudnessdata and the statistical perceived loudness data for the respectiveplurality of different stimulus having the at least some loudness levelscorresponding to those of the statistical perceived loudness levels; andthe sub-system is configured to automatically use the offsets toautomatically adjust the first map and create a second map based on theadjustment; and the sub-system configured to automatically configure thehearing prosthesis configures the hearing prosthesis by loading thesecond map into the hearing prosthesis.
 15. The system of claim 13,wherein: the at least some loudness levels corresponding to those of thestatistical perceived loudness data includes at least some loudnesslevels that are either at or proximate to the statistical perceivedloudness levels.
 16. The system of claim 13, wherein: the action ofconfiguring the hearing prosthesis includes adjusting a current levelregime of the hearing prosthesis such that applied stimulation at thecurrent levels of the current level regime at least results in aperceived loudness that at least approximately corresponds to those ofthe statistical perceived loudness for a given stimulus.
 17. The systemof claim 13, wherein: the sub-system configured to configure the hearingprosthesis based on the obtained statistical data and the obtainedrecipient-specific loudness data is configured to automaticallyconfigure the sub-system configured to configure the hearing prosthesisbased on the obtained statistical data and the obtainedrecipient-specific loudness data.
 18. The method of claim 1, furthercomprising: determining a current level corresponding to a thresholdlevel for a recipient of the hearing prosthesis; and determining acurrent level corresponding to a comfort level for the recipient,wherein the adjustment of the at least one of the respective currentlevels results in a current level located between the current levelcorresponding to the threshold level and the current level correspondingto the comfort level.
 19. The method of claim 7, wherein the actions of:obtaining data indicative of respective perceived loudness levels forthe plurality of hearing percepts respectively evoked based onrespective different stimulus having respective first different loudnesslevels; and obtaining data indicative of normalized loudness levels fornormal hearers for the respective different stimulus having respectivedifferent first loudness levels, is not executed by: (i) empiricallymeasuring, using a system, by stimulating each electrode of a cochlearimplant implanted in a recipient from which the respective perceivedloudness levels are obtained, with a known current, one at a time; (ii)measuring voltage at each non-stimulated electrode; or (iii) estimatingvalues along a diagonal of a transimpendence matrix by linearextrapolation of the values surrounding the diagonal values.
 20. Themethod of claim 7, further comprising, completely separate and beforethe action of obtaining data indicative of respective perceived loudnesslevels: (i) empirically measuring, using a system, by stimulating eachelectrode of a cochlear implant implanted in a recipient from which therespective perceived loudness levels are obtained, with a known current,one at a time; (ii) measuring voltage at each non-stimulated electrode;and (iii) estimating values along a diagonal of a transimpendence matrixby linear extrapolation of the values surrounding the diagonal values.21. The method of claim 1, further comprising: determining a currentlevel corresponding to a threshold level for a recipient of the hearingprosthesis; and determining a current level corresponding to a comfortlevel for the recipient, wherein the adjustment of the at least one ofthe respective current levels results in a plurality of differentcurrent levels located between the current level corresponding to thethreshold level and the current level corresponding to the comfortlevel.